Imaging Neurotransmitters In Vivo Using Functionalized Carbon Nanotubes

ABSTRACT

Imaging based detection of changes in extracellular neurotransmitter concentration in living tissue is achieved using novel nanotube-based sensors. The sensors are functionalized, neurocompatible single-walled carbon nanotubes (SWNT) comprising an adsorbed neurotransmitter analyte selective polynucleotide.

INTRODUCTION

Neurotransmitters play a central role in complex neural networks byserving as chemical units of neuronal communication. As a result,spatiotemporal neurotransmitter sensing has the potential to profoundlyimpact on our understanding of how the brain works, and presents a newplatform by which to validate the function of neurological drugs.Therapeutic drugs that target neurotransmitter release are usedubiquitously to treat a vast array of brain and behavioral disorders:for over 60 years, drugs that alter, mimic, or block dopamine haveformed the core arsenal for the treatment of neurological disorders suchas depression, addiction, schizophrenia, anxiety, Parkinson's disease,and social autism spectrum disorder. However, currently in neuroscience,few analytical methods exist that can detect neurotransmitters with highspatial and temporal resolution in vivo in extracellular space. Thedifficulty of in vivo analyte detection emanates from the opticaldensity of the brain, and its chemical complexity: Brain tissue scattersmost wavelengths of light currently used to perform biological imaging,and neuronal tissue has an abundance of biomolecules that are chemicallyor structurally similar to the neurotransmitters we wish to detect.Furthermore, neurologically relevant processes occur at technicallychallenging size (nano) and time (millisecond) scales. Current tools todetect neurotransmitters have shortcomings in five broad areas that areaddressed by our technology. (i) electrochemical-based tools don't havethe selectivity to differentiate between molecules of similar redoxpotentials, (ii) electrochemical-based tools don't have appreciablespatial resolution (limited to millimeters), (iii) electrochemical toolscan scar tissue limiting use, (iv) fluorescence-based tools don't haveappreciable ability to report changes in extracellular concentration,and (v) and fluorescence based tools can photobleach, and may havelimited use (due to load re-load requirements in case of fluorescentfalse neurotransmitters). Relevant literature: Kruss et al., J. Am.Chem. Soc. 2014, 136, 713-724; Tu et al., Nature 460, 250-253 (9 Jul.2009)

SUMMARY OF THE INVENTION

We disclose an optical molecular recognition platform that utilizespolymer conjugated carbon nanotubes for the detection ofneurotransmitters for use in biological samples in vitro and in vivo,including a physiological fluid like saliva or cerebral spinal fluid, aswell as brain tissue, including intact brain and brain portions, such asslices . We disclose the use of polymer-functionalized carbon nanotubesfor in vivo molecular detection of neurotransmitter analytes, and weexemplify our invention using the detection of neurotransmitters in alive slice of brain tissue. Our invention uses the optical properties ofpolymer-functionalized carbon nanotubes to detect the analyte. Detectionof neurotransmitters is accomplished both in space and time, reversibly.Our sensors are biocompatiable and neurocompatible, and allow opticalimaging of neurotransmitter spatial distribution, concentration, anddynamics in real time and in living tissue. The invention takesadvantage of favorable fluorescence properties of carbon nanotubes, suchas carbon nanotube emission in the near infrared (a region of relativeoptical tissue transparency), and non-photobleaching fluorescence. Thenear infrared emission is minimally scattered in biological systems,enabling their use in deep tissues. The non-photobleaching fluorescenceof our neurotransmitter sensors enable their use in hours-longexperiments. Infrared emission and non-photobleaching fluorescencebenefits are features that are lacking in modern fluorescence imagingmethods.

In embodiments, the invention provides;

-   -   measurement of neurotransmitter levels or dynamics in        neurotransmitter concentrations using optical imaging in tissue        or fluid; these measurements may be performed in the brain or        peripheral nervous system of anesthetized or awake animal        subjects, or in reduced brain preparations (e.g. brain slices of        any species);    -   dynamic spatial and temporal readout of neurotransmitter        concentrations in any part of the brain or peripheral nervous        system. It may also be applied to measure and image        neurotransmitter concentrations in tissue or fluid samples that        may contain neurotransmitters;    -   monitoring neurotransmitter levels in biological solutions or        preparations; for example in saliva or cerebrospinal fluid;    -   brain imaging for use in various settings such as diagnostics in        health care facilities, teaching, and research in academic        settings;    -   methods and compositions to quantitatively evaluate and or        validate the mechanism of action and/or efficacy of new and or        established drugs or other therapeutics that target        neurotransmission. Examples of such drugs include Levodopa and        dopamine antagonists (e.g. Ropinirole, Pramipexole, Loxapine,        Thioridazine, Thiothixene, Trifluperidol), agonists (e.g.        Modafinil, Rotigotine, Dizocilpine, Ciladopa, Fenoldopam,        Rotigotine, Memantine), reuptake inhibitors (e.g.        Desoxypipradrol, Troparil, Benztropine, Mesocarb, Mazindol,        Altropane), and releasing agents (e.g. Phenmetrazine, Mefenorex,        Amfecloral, Fenproporex). Neurotransmitter measurements may be        achieved in either blood, saliva, CSF, brain tissue, brain        slices, and or anesthetized or awake and behaving animals;    -   monitoring progression of brain diseases;    -   methods and compositions for identifying parts of the brain that        have suffered trauma (i.e. traumatic brain injury) and can be        used to determine if (and to what extent) that injury site has        affected its ability to undergo normal neurotransmission        behavior;    -   methods and compositions to determine how external stimuli        (perceptual, social, chemical etc.) affect neurotransmission in        the brain of awake and behaving animals;    -   functionalized, neurocompatible single-walled carbon nanotubes        (SWNT) and their use for imaging of neurotransmitters in vivo,        in live animals; and/or    -   sensors configured to image complex neural physiology by        monitoring the spatial and temporal dynamics of        neurotransmitters in live brain tissue.

In an aspect the invention provides a functionalized, neurocompatiblesingle-walled carbon nanotube (SWNT) comprising an adsorbedneurotransmitter analyte selective polynucleotide covalently bound to aneurocompatible polyethyleneglycol (PEG).

In embodiments:

-   -   the polynucleotide is ssDNA or ssRNA;    -   the polynucleotide has a periodic purine-pyrimidine pattern, or        any combination of purine and pyrimidine bases;    -   the polynucleotide is polyGT is (GT)n, wherein n is an integer        2-500, or 3-150, or 4-30, or about 15;    -   the analyte is a neurotransmitter selected from a catecholamine        (e.g. epinephrine (adrenaline), norepinephrine (noradrenaline),        and dopamine), histamine, 5-hydroxytryptamine (serotonin),        γ-aminobutyric acid (GABA), glutamine, glutamic acid or a        neurotransmitter metabolite selected from        L-3,4-dihydroxyphenylalanine (L-dopa), 3,4-Dihydroxyphenylacetic        acid (DOPAC), homovannilic acid and tyramine; and/or    -   the PEG is PEG MW 200-40000, or 400-20000, or about 5000.

In another aspect the invention provides a functionalized,neurocompatible single-walled carbon nanotube (SWNT) comprising anadsorbed dopamine-selective polynucleotide of sequence (GT)₆.

In embodiments:

-   -   the polynucleotide is covalently bound to a neurocompatible        polyethyleneglycol (PEG); and/or    -   the PEG is PEG MW 200-40000, or 400-20000, or about 5000.

The invention also provides methods of imaging neurotransmitters in vivousing functionalized, neurocompatible nanotube sensors, particularlywherein the sensors are delivered to the brain of a live mammal, such aswherein the changes in extracellular neurotransmitter concentration aredetected in neural tissue, cerebrospinal fluid, blood or saliva, andparticularly wherein the changes are detected in neural tissue.

The invention encompasses all combination of the particular embodimentsrecited herein, as if each combination had been laboriously recited.

DESCRIPTION OF PARTICULAR EMBODIMENTS OF THE INVENTION

Unless contraindicated or noted otherwise, in these descriptions andthroughout this specification, the terms “a” and “an” mean one or more,the term “or” means and/or and polynucleotide sequences are understoodto encompass opposite strands as well as alternative backbones describedherein.

It is understood that the examples and embodiments described herein arefor illustrative purposes only and that various modifications or changesin light thereof will be suggested to persons skilled in the art and areto be included within the spirit and purview of this application andscope of the appended claims. All publications, patents, and patentapplications cited herein, including citations therein, are herebyincorporated by reference in their entirety for all purposes.

We disclose an optical molecular recognition platform that utilizespolymer conjugated carbon nanotubes for the detection ofneurotransmitters for use in vivo. When a polymer is non-covalentlyconjugated to the surface of a single-walled carbon nanotube (SWCNT), acorona phase forms with unique molecular recognition sites for specificbiomolecules (in this case, neurotransmitters). When an analyte binds tothe polymer-nanotube conjugate, the corona phase is perturbed, changingthe optical properties of the nanoparticle. This modulation in thefluorescent emission of the nanoparticle is reversible, and serves asthe recognition signal for the analyte. This fluorescence modulation,when measured using fluorescence microscopy, provides a readout ofneurotransmitter concentration with spatial and temporal resolution forin vivo experiments. Our method holds distinct advantages over otheroptical methods because of the near infrared emissivity of carbonnanotubes where scattering by biological tissue is minimal.

Adding to the advantages of our platform is the optical stability ofcarbon nanotubes that allow extended imaging with no loss offluorescence output, a property critical for performing long-termimaging experiments that have yet to be implemented with otherfluorescent probes. Our sensors convey information on neurotransmitterconcentration on size and time scales that few other tools inneuroscience provide. The selectivity of the sensors for a particularneurotransmitter ensures that the signal transduced is that of aparticular neurotransmitter. Some of the general utilities for ourinvention are:

Detection of neurotransmitter release in viable neural tissue (in vivo);

Conveying neurotransmitter concentration information on spatial andtemporal scales appropriate to study physiological processes in livebrain tissue;

Probing complex neural circuitry by monitoring changes inneurotransmitter concentration in different parts of the brain in realtime;

Probing how neural plasticity is affected (or affects) neurotransmitterrelease;

Examining effect of pharmaceutical drugs on brain function as conveyedby changes in neurotransmitter concentration;

Monitoring changes in neurotransmitter concentration during behaviorstudies involving awake and behaving animals;

Monitoring changes in physiology (function) caused by pharmaceuticalagents, brain disorders or traumatic injuries; and/or

Imaging brain activity for diagnostic or therapeutic purposes.

Our SWCNT nanosensors are neurocompatible, emit in the near-infraredspectrum and offer a new optical method for detection ofneurotransmitters. The optical methods enable greater spatial resolutionand chronic recording. In combination with other imaging methods canprovide a wealth of new information about release and diffusion, theaction of drugs with abuse potential or therapeutic application.

Our invention enables non-invasively imaging dynamic neuronal activityacross large swaths of the brain, making it uniquely suited to enablingneurotransmitter imaging in real-time in awake and behaving animals; forexample, the invention may be used to validate drugs (antipsychotics,antidepressants, stimulants, etc) that target neurotransmission. Theinvention provides imaging brain circuitry on spatiotemporal scalesappropriate for neuroscience and for drug validation.

Competing methods include (1) Fast scan cyclic voltometry andamperometry (FSCV), (2) CNiFERs, and (3) fluorescent falseneurotransmitters (FFNs). FSCV and amperometry are electrode-basedmethods that use oxidation of catecholamines at a carbon fiber to reportcatecholamine levels. CNiFER is cell-based and is based on slow Gprotein-coupled receptor responses. FSCV and CNiFER methods have lowspatial resolution and recording sites are placed blind to axon site.These methods have not been sufficient to enable continuous andspatially and temporally-relevant measurements of dopamine and othermodulatory neurotransmitters in the neocortex. Fluorescent falseneurotransmitters (FFNs) can be used to study dopamine release but arenot easily loaded and reloaded for long term use. FFNs do not reportneurotransmitter levels in extracellular space. Calcium imaging can showbouton activity preceding release but may not report longer term releaseand do not report neurotransmitter levels in extra cellular space.

Advantages of our sensors in contrast to FSCV include: Cyclicvoltammetry provides little in the way of spatial resolution of analytesit measures. Cyclic voltammetry probes measure millimeters at best, andmust be inserted directly into brain tissue to acquire a reading.Positioning next to release sites is not feasible when they are sparse.In contrast, our nanosensors are nanometers in size (1×200 nm) and canbe injected directly into brain tissue in a relatively non-invasivemanner Compatible imaging methods can be used to determine distance fromrelease sites and enables detection with high spatial resolution forcomparing brain regions or for following diffusion from a site. Thenanometer-scale size of our sensors enables us to report onnanometer-scale spatial changes in neurotransmitter concentration, whichis relevant to the size of the synaptic cleft (300 ±150 nm) in whichneurotransmission occurs between neuronal cells. (ii) FSCV has lowselectivity for a neurotransmitter target of interest: if analytes withsimilar redox potentials exist within the region of interest, thissignal will confound the signal from dopamine release. Cyclicvoltammetry readings will report on the presence of any molecules with asimilar redox potential to the target neurotransmitter. In contrast, ournanosensors are selective for a neurotransmitter of interest. (iii) Costand user-friendliness. Compared to our nanosensors, FSCV is expensive,requires high degree of expertise to operate, and is invasive. (iv) FSCVand comparable methods are susceptible to probe fouling, such that eachsubsequent reading may exhibit hysteresis that is a function ofelectrode fouling. In contrast, our sensors have a nanosecond residencetime on the nanosensors surface (as determined by molecular dynamicssimulations), suggesting that there is no fouling of our sensors bychelation of biomolecules on the sensor surface. Our data show severaliterations of dopamine detection in an acute brain tissue slice,exemplifying the non-fouling nature of our sensors.

Advantages of our sensors in contrast to fluorescence based techniquesinclude (i) infinite fluorescence lifetimes (no photobleaching)enabling—for the first time—measurement of neurotransmitters forhours-long timescales in artificial cerebrospinal fluid (aCSF). (ii) Ournanosensors are reversible. CNiFER can only report on the cumulativeGPCR activity. FFNs only report on neurotransmitter release. Our sensorscan directly report both the appearance but also the disappearance ofneurotransmitters in extracellular space. This enables us to measureboth neurotransmitter release and neurotransmitter re-uptake, both ofwhich are key elements of modulatory neurotransmission. In areas ofsparse release, we may also be able to visualize diffusion from arelease site, which would also add new ability. (iii) Our nanosensorsare nano-scale. CNiFER are the size of HEK293 cells that encode theirsignal (10-15 μm). Therefore, CNiFER are inherently more ‘invasive’ wheninserted into brain tissue, as they require a larger accommodationvolume. Additionally, CNiFER can only report on indirect GPCR activitywithin a spatial limit of detection that matches their size (tens ofmicrons). Conversely, our sensors are nanometers in size (1 nm×200 nm)and can be used to report on nanometer-scale spatial changes inneurotransmitter concentration, which is relevant to the size of thesynaptic cleft (300±150 nm) in which neurotransmission occurs betweenneuronal cells. (iv) CNiFER cells respond on the timescale of seconds tominutes, whereas our sensors respond on millisecond timescales. In otherwords, from the time when a neurotransmitter is released until thesensor responds to its presence, CNiFER cells will have a second tominute-long time lag. Our sensor's millisecond temporal responsivitymatches the time-scale upon which neurotransmitters are released in thebrain. (v) Our sensor signals can penetrate tissue and bone with anear-infrared signal. Unlike other fluorescent methods, we can acquirefluorescence signal with less scatter from our sensor through braintissue and through bone (cranium) tissue. We demonstrate thebone-penetrating capabilities, in which we have placed our sensors ontop of a mouse cranium, and monitor the fluorescence of thesenanosensors upon addition of neurotransmitter. We can detect a clearincrease in fluorescence upon addition of neurotransmitter through themouse cranium.

A significant utility of our invention lies in its ability to help probecomplex neural physiology by monitoring the spatial and temporaldynamics of neurotransmitters in live brain tissue; for example, theeffects of pharmaceutical therapies on brain function can be studied inreal time.

In an aspect the invention provides a functionalized, neurocompatiblesingle-walled carbon nanotube (SWNT) comprising an adsorbedneurotransmitter analyte selective polynucleotide covalently bound to aneurocompatible polyethyleneglycol (PEG).

SWNTs comprising an adsorbed neurotransmitter analyte selectivepolynucleotide are known in the art, and the methods of making andcriteria for selecting analyte selective polynucleotides areestablished. Suitable polynucleotide are typically, ssDNA or ssRNA,which may be present in a variety of structural conformations. Preferredpolynucleotides have a periodic purine-pyrimidine pattern, such aspolyGT is (GT)n, wherein n is an integer, such as 2-500, or 3-150, or4-30, or in a particular example, about 15.

We have validated the disclosed methods with a variety ofneurotransmitter analytes, including catecholamines, histamine,5-hydroxytryptamine (serotonin), γ-aminobutyric acid (GABA), glutamine,glutamic acid, L-3,4-dihydroxyphenylalanine (L-dopa),3,4-Dihydroxyphenylacetic acid (DOPAC), homovannilic acid and tyramine.

Suitable neurocompatible polyethyleneglycol (PEG) components are readilydetermined empirically, confirmed by lack of effective toxicity, asexemplified below, and include a variety of structures (e.g. branching)and molecular weight, including PEG MW 200-40000, or 400-20000, or about5000.

To demonstrate our nanosensor's utility in living brain tissue, wedetail experiments herein in which the release of endogenousneurotransmitter is monitored from acute brain slices stimulated by highpotassium (K⁺) containing buffer solution. We describe the synthesis ofthe sensors, detail the preparation of brain slices embedded with ourneurotransmittersensors, and provide experimental details for theimaging of brain slices embedded with our nanosensors.

EXAMPLES 1. Imaging Dopamine in Brain Tissue Using Synthetic InfraredNanosensors

The optical nanosensors are synthesized by suspending single walledcarbon nanotubes in pegylated (GT)₁₅ DNA by probe tip sonication in a100 mM NaCl buffer solution. The pegylation of the DNA strand can beachieved by reacting maleimide end-modified polyethylene glycol (PEG, 3kDa) with a 5′ thiolated (GT)₁₅ DNA. The pegylated DNA is then sonicatedfor 10 minutes at ˜5 W power setting. Finally, the sonicated mixture iscentrifuged to remove unsuspended nanotubes, and the recoveredsupernatant characterized using a UV-Vis spectrometer. This simple andeasily scalable process gives a stable sensor suspension that can bestored at room temperature for extended time periods. The user candilute the suspensions to desired nanotube concentrations for in vivoand in vitro use.

Acute brain slices are prepared from anesthetized mice. The brain isquickly extracted from the skull and mounted on a vibratome for slicing.The vibratome was pre-chilled to 4° C. and the sample tray filled withO₂ saturated aCSF buffer. At all times, the brain and recovered brainslices were kept in continuously gassed (95% O₂, 5% CO₂) aCSF buffer at4° C. Sensors were diluted to a nanotube concentration of 25 mg/L in PBS(phosphate buffered saline) before being injected into the brain.Approximately 20 μL of sensor volume was injected into the mounted brainusing Hamilton Neuros Syringes, from which 300 μm slices were recovered.After recovery of 3 such slices, an additional 20 μL of sensor wasinjected into the brain, after which brain slices continued to berecovered. 20 μL sensor volume was injected for every 3 slices recoveredfrom the brain until enough brain slices were recovered for theexperiment. Each 20 μL volume injection was delivered into three to fivedistinct regions to enable neurotransmitter detection in various regionsof the brain.

Sensors are delivered into the brain via injection. The injection siteand its periphery will house a bolus of sensors, which detectneurotransmitter molecules and changes in neurotransmitter concentrationas neurotransmitter diffuses out of their point of release. Owing totheir small size, some of our sensors may be inside the synaptic region(interface between two neuronal axons where neurotransmitter releasetakes place); however, a significant portion of the injected sensorswill be extrasynaptic in location. Regardless of their location,diffusion of neurotransmitters is the primary mechanism by whichneurotransmitters signal between cells. Once in contact withextracellular sensors, neurotransmitter molecules (or other specificsensor analytes) cause conformational changes of the pegylated (GT)₁₅DNA on the surface of the nanotube, resulting in modulation offluorescence behavior; in the case of neurotransmitter detection, themodulation produces a rapid increase in the fluorescence of the carbonnanotubes.

The depolarization wave that triggers release of neurotransmitter can beelicited using electrical, chemical, or optical stimulation. For ourdemonstration, we use chemical stimulation using a high 15-35 mMpotassium (K⁺) aCSF buffer. The high concentration of potassium causesan ion imbalance between the cytoplasmic and extracellular environment,which causes neuronal membrane depolarization and neurotransmiterrelease.

We imaged direct nanosensor-based neurotransmitter release in braintissue in four acute slices, and representative intensity-time traces.When neurotransmitter is released from neurons, the near-infraredfluorescence intensity of our sensors increases. The increase inintensity is normalized and presented as a plot against time in fourdifferent brain slices. Our results show the near-infrared fluorescencespectra of our sensors, and the characteristic multi-peak emission ofour sensor emission profile. This spectrum serves to confirm that thesensor intensity increase imaged in the brain tissue slice is caused bymodulations in the fluorescent properties of the nanotubes (as a resultof neurotransmitter release), and not an artifact caused by changes inbaseline tissue fluorescence.

We also tested the reversibility of our sensors in living neural tissue.Reversibility demonstrates that once neurotransmitter causesconformational changes that increase fluorescence intensity of oursensors, the subsequent removal of neurotransmitter from theextracellular space can reverse the fluorescence intensity increase, ineffect resetting our sensors for detection of subsequentneurotransmitter release events. Sensor reversibility is vital tomonitoring dynamic neurotransmitter concentrations, and a featurelacking in many existing technologies for neurotransmitter detection.

We have confirmed our neurotransmitter nanosensor is functional in exvivo striatal tissue by using high K+ to drive bulk neurotransmitterrelease, for multiple stimulation and wash cycles, over the course of 80minutes. These data also reduce concerns about potential “biofouling” inwhich the sensor is activated or inactivated by non-specific bindingwhen placed in tissue, or in which the sensor degrades after repeateduse or after extended time.

In vitro experiments show the neurotransmitter nanosensors can reportneurotransmitter concentrations that range from 100 nM to 0.1 mM, arange relevant to endogenous neurophysiology. At the single sensorlevel, we can detect picomolar (pM) quantities of neurotransmitter. Thethrough-cranium neurotransmitter detection capabilities we demonstrate,enabled by the tissue and bone-transparency of infrared fluorescencewavelengths emitted by our sensors, indicate our sensors will enabledetection of neurotransmitters in an intact brain structure, through thecranium bone.

We have applied our model of sensor response in striatal tissue to theexpected pattern of neurotransmitter release as detailed in theliterature, for both positive and negative reward prediction errorresponses. We estimate that neurotransmitter release driven by a shiftfrom tonic firing at 5 Hz to a phasic burst at 20 Hz for 500 msec (apositive reward prediction error) should be induce a deltaF/F of 0.27using bulk phase detection. Movement from a tonic rate at 5 Hz to 1 Hzpause for 500 msec (a negative reward prediction error) should produce adelta F/F of −0.07. These delta F/F estimates are modest but sufficientand are comparable to levels reported in experiments using geneticallyencoded calcium indicators such as GCAMP for functional imaging inrodents. These estimates indicate that this sensor is a useful tool fordetection of changes in modulatory neurotransmitter levels relevant tobehavioral studies in awake behaving animals.

We have tested and confirmed imaging of a panel of neurotransmitteranalytes, including epinephrine (adrenaline), norepinephrine(noradrenaline), dopamine, 5-hydroxytryptamine (serotonin), glutamicacid, L-3,4-dihydroxyphenylalanine (L-dopa), 3,4-Dihydroxyphenylaceticacid (DOPAC), homovannilic acid and tyramine

2. Molecular Recognition Mechanisms Revealed in DNA-Wrapped CarbonNanotubes

In this example we demonstrate molecular recognition mechanismsunderlying the SWNT sensing activity. Varying the length of DNA polymerswrapping SWNTs yielded highly selective sensors for molecular analytesdopamine and norepinephrine. Molecular dynamics studies identified thatthe selectivity in these new sensors originates from DNA polymers thatassume circular conformations on SWNTs, and perfectly wrap the SWNT oncealong its circumference. We identify that DNA conformations createdistinct modulations of the electrostatic environment within SWNT, whichcan lead to enhanced localization of the exciton. We also observe chargetransfer to SWNTs in ssDNA-SWNT composites, which can influence excitonrelaxation pathway and relaxation rates. Surfactant exchange revealsdopamine molecular recognition mechanism: polynucleotide surfacecoverage.

To identify the mechanisms that enable selective molecular recognitionof dopamine by SWNT-based optical nanosensors, we performed all-atommolecular dynamics (MD) simulations, quantum mechanical (QM)calculations, and fluorescence imaging of the (GT)₁₅-SWNT nanosensorselective for neurotransmitter dopamine. MD simulations reveal thatpolymer length dictates the structure of the polymer on the SWNT,whereby 12 nucleoside-length single-stranded DNA (ssDNA) polymers formrings around SWNT instead of helices. The SWNT surface-adsorbed polymergenerates patterns of electrostatic potentials on the SWNT surface andstrongly localizes excitons, leading to a prevalence of non-radiativeexciton recombination in SWNT. MD and QM calculations identify chargetransfer between the polymer wrapping and the SWNT as the mechanism ofPL attenuation, which can be reversed in the presence of theneurotransmitter analyte. Quantum mechanical (QM) calculations show thatadsorbed nucleosides of the polymer dope the SWNT, forming chargetransfer sites along the nanotube axis. In the presence of these dopingsites, strongly localized excitons recombine efficiently through adominant non-radiative multiphonon decay process. This decay isabolished or severely slowed in the presence of dopamine, leading to thebrightening of photoluminescence (PL). We validate our calculations withfluorescence spectroscopy and microscopy of SWNT nanosensors, anddemonstrate that we can implement our QM and MD strategy to controlexciton recombination and analyte selectivity to discover a newfluorescent sensor for neurotransmitter norepinephrine. Our workexplores the wide range of time-scales over which fluorescent probesselectively photoluminesce in the presence of neurological targets:charge transfer (femtosecond via QM calculations), selective analytebinding and exciton recombination (nanosecond via MD simulations), andneurotransmitter imaging (millisecond via infrared microscopy).

MD simulations show DNA polymer length modulates helix-to-ringtransition on SWNT. Variations in the fluorescence (the PL quantumyield) of SWNTs wrapped by different polymers can depend on the chemicalcomposition of the polymers, interaction types and strengths, and thephysical parameters of the SWNT environment, such as the dielectricscreening. We implement MD simulations of known SWNT-based dopaminenanosensor (GT)₁₅-SWNT to elucidate how the polymer creates patterns inthe electrostatic environment of the SWNTs, and to examine how thisenvironment affects SWNT PL. The initial states of ssDNA-SWNT systemswere based on reported structures of ssDNA adsorbed to SWNT, whichdemonstrated that ssDNA polymers wrap SWNTs helically. Our MDsimulations show that (GT)₁₅ ssDNA remains equilibrated onto the SWNTsurface in a helical structure within the 200 ns simulation length,consistent with previous studies, and showed no significant structuraldeviations from its initial helical conformation.

To examine the electrostatic effect of the ss-(GT)₁₅ polymer on SWNT, wecalculated the electrostatic potential induced by the ss-(GT)₁₅ at theSWNT surface. The calculated potential includes all molecules present inthe SWNT environment: the ssDNA polymer, water, and ions, including theNa⁺ cations adsorbed over long timescales within DNA pockets. We findthat ss-(GT)₁₅ induces regions of negative and positive electrostaticpotential as a ‘footprint’ under the polymer, which extend ˜4 nm incontiguous length, and roughly follow the helical pattern of the ssDNA.

Motivated by the observed electrostatic footprinting of polymersadsorbed to SWNT, we further explored alternate (GT)_(n) ssDNApolymer-SWNT structures, where n indicates ssDNA polymers containing avarying number of repeating (GT) units. While ssDNA molecules thatencapsulate SWNTs several times are observed to adopt helicalconformations, shorter ssDNA oligonucleotides adopt different surfaceadsorbed patterns, which can afford a unique control parameter overelectrostatic footprinting and SWNT exciton recombination. Inparticular, SWNTs that are widely used for fluorescence imaging andsensing have ˜1.2 nm diameters, which can accommodate a singly wrapped12-mer (4.08 nm long) oligonucleotide. Thus, we performed MD simulationsof (GT)₆ oligonucleotide initially helically equilibrated to the surfaceof a (9,4) SWNT, to replicate the initial conditions of the simulated(GT)₁₅-SWNT system. During a short 20 ns simulation, (GT)₆ polymerrearranged from its initial helical conformation to a ring-likestructure; such helix-to-ring transitions were reproducibly observedin >5 independent MD simulations. While the system contains a singlessDNA molecule, fluorescent SWNT nanosensors typically contain manyssDNA molecules adsorbed onto a single SWNT. Therefore, to betteremulate experimental conditions, we examined multiple ssDNA-(GT)₆polymers wrapping the SWNT. Following simulation, we again observehelix-to-ring transition for all (GT)₆ polymers. The DNAs in ringconformations are highly ordered, as evidenced by distinct sharp peaksthat appear at approximately equal intervals in the radial distributionfunction of DNA phosphate groups. Electrostatic footprinting induced bythe ring-like structures of (GT)₆ polymers on SWNT is observed,following the physical adsorption pattern of the electrostatic potentialinduced by the (GT)₆ polymer. The resulting electrostatic potential mapon the SWNT surface appears in distinct ring-like regions of alternatingpositive and negative potential along the SWNT surface, where eachelectrostatic pocket measures ˜1.5 nm in contiguous length. The negativeelectrostatic potential pockets are observed primarily beneath guaninenucleotides, while the positive electrostatic potential pockets areobserved beneath thymine nucleotides.

Electrostatic footprinting of SWNT by circumference-length (GT)_(N)polymers yield high turn-on sensors for dopamine and norepinephrine. Forin vivo applications of neurotransmitter nanosensors, a strongfluorescence turn-on response is necessary. Prior work shows that thefluorescence intensity of ss(GT)₁₅-SWNT increases by as much as 90% uponexposure to 100 μM dopamine At physiological concentrations (˜1 μM), theexpected ΔF/F is on the order of 30%. Dopamine addition to thess(GT)₁₅-SWNT sensor does not perturb the SWNT absorption cross section,thus the fluorescence intensity increase results from an increase indopamine-induced SWNT quantum efficiency. Guided by the theoreticallypredicted electrostatic confinement of SWNT excitons by (GT)₆ polymers,we synthesized a (GT)_(N) based ssDNA polymer library to probe theeffects of polymer conformation on nanosensor sensitivity andselectivity to neurotransmitter dopamine We produced a library of(GT)_(N) ssDNA sequences for N=1, 4, 6, 7, 8, 12, 15, 19, 22, 26, and 30using a previously-described protocol. All sequences from N=4 to N=30produced DNA-SWNT suspensions, with the exception of N=1 that did notsuspend SWNT. We measured each (GT)_(N)-SWNT sensor's response to 100 μMdopamine Consistent with previous results, dopamine addition increasesSWNT fluorescence for all sequences. We observe a surprisinglength-dependent trend in nanosensor response to 100 μM dopamine, forwhich the previously reported (GT)₁₅-SWNT nanosensor represents anapparent minimum (ΔF/F₀=45%), and (GT)₆-SWNT a maximum (ΔF/F₀=3500%).Short (GT)_(N) repeats (N=4, 6, 7, 8) yield ΔF/F₀=1400%, 2400%, 1700%,and 1000% in response to 100 μM dopamine, respectively, for the (9,4)SWNT chirality. For longer sequences (N=12, 15, 19, 22, 26, 30), weobserve corresponding ΔF/F₀=45%, 45%, 50%, 60%, 40%, and 150% inresponse to 100 μM dopamine, respectively. We identify ssDNA polymerscapable of ring-like electrostatic footprinting as having strong turn-onresponses to dopamine.

We next examined the baseline fluorescence intensity of equimolaraliquots of each DNA-SWNT suspension in our library, we observe thatshort (GT) repeat sequences (N=4, 6, 7, 8) exhibit strongly quenchedbaseline fluorescence, representing 25%, 5%, 15%, and 40% of thebaseline fluorescence exhibited by (GT)₁₅-SWNT when compared at the(9,4) chirality peak. Conversely, long sequences (N>=12) exhibitapproximately the same degree of baseline fluorescence as compared to(GT)₁₅-SWNT. In general, the pre-dopamine fluorescence of (GT)_(N)-SWNTsuspensions is lower for sequences where N≤8, indicating thatpolynucleotide sequences exceeding roughly twice the average SWNTcircumference in length will adopt a helical SWNT-adsorbed structure, asconfirmed by our MD simulations of (GT)₁₅-SWNT and (GT)₆-SWNT. We thusidentify polymer length as a key modulator of SWNT fluorescence quantumyield, which can be exploited for maximizing nanosensor ΔF/F₀ signal. Wefurther identify the (GT)₆-SWNT complex as the most suitable nanosensorfor imaging dopamine and norepinephrine. DNA-SWNT absorption spectraremain invariant to the addition of dopamine, further indicating thatquantum yield increases are what drive the increase in fluorescence forshort and long sequences.

To validate the potential in vivo imaging use of (GT)₆ SWNT for dopamineand norepinephrine, we developed fluorescence response curves for(GT)₆-SWNT suspension by varying concentrations of norepinephrine anddopamine We fit our experimental data using the Hill equation to obtainthe dissociation constant for sensor-analyte interaction. We determinedthe dissociation constants to be 15 μM for norepinephrine and 20 μM fordopamine. Both dopamine and norepinephrine fluorescence turn-on behavioris suitable for measuring neurotransmitter concentrations inbiologically-relevant regimes encompassing tonic and phasic firingindicating these sensors are suitable for in vivo imaging of modulatoryneurotransmission. A burst of activity from dopaminergic neurons in thestriatum can yield local dopamine concentrations on the order of 1 μM to5 μM. The strong turn-on response of ss(GT)₆-SWNT nanosensors is crucialfor studying the slow tonic firing of dopaminergic neurons whereextracellular dopamine concentrations vary transiently from 10 nM to 100nM. Under such neuronal activity, only (GT)₆-SWNT sensors produce astrong ΔF/F₀ signal to enable in vivo use, and discriminate betweentransience in tonic firing. We note that compared to the previouslyreported ss(GT)₁₅ based dopamine sensor, the dopamine-inducedfluorescence response from our ss(GT)₆ sensor is nearly an order ofmagnitude higher, and significantly more selective toward dopamine andnorepinephrine, showing nearly no cross-responsivity for otherneurologically-relevant analytes in our screening library. We owe thisincreased selectivity to the molecular modes of interaction between thecatecholamine and nucleosides on the DNA polymer of ss(GT)₆-SWNT, as wedescribe below. Control experiments with (C)₃₀-SWNT and (C)₁₂-SWNT showthese DNA-SWNT conjugates are non-responsive when exposed to eitherdopamine or norepinephrine, attributing the selectivity of ournanosensors to the (GT) base sequence, and the sensitivity to thepolymer length and subsequent SWNT electrostatic footprinting.

Polymer length modulates stability of polymer on SWNT. We examined thestability of all (GT)_(N)-SWNT suspensions using fluorescence andabsorbance spectroscopy. To rule out the possibility that spontaneousDNA polymer rearrangement contributes to the large increase innanosensor fluorescence after addition of dopamine, we measured thetime-dependent fluorescence of all (GT)_(N)-SWNT suspensions usingfluorescence spectroscopy. Prior work shows that DNA-SWNT fluorescencestability directly correlates with DNA polymer stability on the SWNT. Totest stability using fluorescence, we diluted all (GT)_(N)-SWNTsuspensions to equimolar SWNT concentrations and measured theirfluorescence spectra over the course of 140 minutes immediatelyfollowing dilution. Most of the (GT)_(N)-SWCNT suspensions we examinedexhibited stable fluorescence (<−15% change) with the exception of(GT)₄-SWNT, which showed a final −40% modulation in fluorescence. Forall (GT)_(N)-SWNT suspensions, the time-dependent fluorescencemodulations were negative, compared to the increase in fluorescenceinduced by dopamine, further confirming that increase in fluorescenceobserved immediately after addition of dopamine is due to the dopamineanalyte, and unlikely to have been caused by volume perturbations orspontaneous polymer rearrangement on the surface of the carbon nanotube.The differences in fluorescence modulation experienced by eachsuspension indicate that polymer length affects the base stackingstability of the (GT)_(N)-SWNT suspensions with an apparent instabilityfor N≤4. Absorbance measurements support the trend observed fromfluorescence measurements. Absorbance measurement of the as-made(GT)_(N)-SWNT suspension exhibits strong absorption at ˜260 nm,suggesting excess, unadsorbed DNA in solution. The absorbance peak at260 nm is abolished by removing unsuspended polymer by filtercentrifugation. Absorbance measurements at the DNA absorbance peakreveal that no ssDNA polymer desorption occurs from any (GT)_(N)-SWNTsample, with the exception of (GT)₄-SWNT that shows appreciable (GT)₄polymer desorption from SWNT after one week at room temperature. Ourresults indicate that (GT)_(N) sequences with N>4 form stablenon-covalent conjugates with SWNT and that SWNT PL modulation observedin the presence of dopamine results from the polymer-mediated modulationin SWNT quantum yield.

Surfactant exchange reveals dopamine molecular recognition mechanism:dopamine-binding pockets from polymer surface coverage. We measured therelative surface coverage of SWNT by (GT)_(N) polymers in our librarywith surfactant exchange experiments. When added ssDNA-SWNT, surfactantsodium cholate (SC) adsorbs to exposed SWNT surface, and can alsodisplace weakly adsorbed DNA regions, causing a solvatochromic SWNTfluorescence peak shift, as reported previously. Addition of 1 wt % SCto (GT)_(N)-SWNT induces solvatochromic shifts in SWNT fluorescencepeaks, with the largest solvatochromic observed for (GT)₄-SWNT, furtherindicating (GT)₄ is the least stably adsorbed sequence on the SWNT.Sequences above N=4 (N=6 to N=30) all showed minimal SC-inducedsolvatochromic shifting, indicating that for polymer lengths >4,polynucleotide polymers remain stably bound to the SWNT. We repeated SCsolvatochromic shift experiments for all (GT)_(N)-SWNT suspensionspre-incubated in 100 μM dopamine Surprisingly, addition of dopamine to(GT)_(N)-SWNT suspensions pre-incubated with dopamine either reduces oreliminates the SC-induced solvatochromic shifting. As such, it appearsthat dopamine stabilizes polymer adsorption onto the SWNT surface, evenfor polymers such as N=4 previously identified to be unstably bound. Wedisclose that dopamine stabilization of (GT) _(N) polymers on SWNTarises from a selective interaction between dopamine and (GT)_(N)-SWNT,and further, that dopamine trapped in these (GT)_(N) polymer bindingpockets enhance PL by direct interaction with the adsorbed polymer andthe SWNT, and as a result of these interactions, the PL quantum yield ofSWNT sensors is selectively enhanced by polymer-induced trapping ofdopamine.

Adsorbed Dopamine Modulates ssDNA Conformation and ElectrostaticPotential at SWNT. To further examine the molecular recognitionmechanism of dopamine by (GT)_(N)-SWNT nanosensors, we performedall-atom MD simulations of ssDNA-(GT)₁₅ and ssDNA-(GT)₆-SWNT in thepresence of dopamine. Several independent MD simulations revealed thatdopamine can influence ssDNA conformations and that dopamine hasmultiple binding poses that are transient.

We prepared representative binding poses of dopamine to ssDNA-(GT)₁₅ andssDNA-(GT)₆-SWNTs. Dopamine can insert into SWNT regions thattransiently have no DNA coverage, and be stabilized by simultaneouslystacking to the SWNT and hydrogen bonding to neighboring DNAsnucleotides. Also, dopamine can bind to ssDNA-(GT)₁₅-SWNT so that itraises neighboring DNA bases. Occasionally, when dopamine stacks onSWNT, DNA nucleotides can also cover dopamine and form stackedsandwich-like structures. The bound dopamine contributes to thepotential created at the SWNT surface. Our poses show the electrostaticpotential beneath dopamine for several representative binding poses onthe SWNT surface. Dopamine binding usually corresponds to extension ofthe electrostatic potential regions. Such modulations in the potentialare likely to affect exciton localization.

Two different mechanisms of binding of dopamine to longer and shorterssDNA wrapping SWNT are indicated. In the case of ssDNA-(GT)₁₅, dopamineis trapped between two ssDNA pitches close to the end of ssDNA-(GT)₁₅where two raised thymine bases trap dopamine However, the mechanism ofdopamine adsorption to ssDNA-(GT)₆-SWCNT is different; here, dopaminebinds between two successive ssDNA-(GT)₆'s. The adsorbed dopamineextends the positive and negative potential domains and leads to excitonsize extension. Opened water windows by adsorbed dopamine between twossDNA-(GT)₆'s enhances the extension of electrostatic potential patternleading to less exciton localization at the SWNT surface and brighter PLresponse of ssDNA-(GT)₆-SWCNT conjugates.

Polymer surface density determines density of dopamine binding sites.Our results thus far demonstrate that the conformation ofsurface-adsorbed ssDNA polymers on SWNT influences SWNT fluorescence andenables tuning of nanosensor responses by affording control over theDNA-SWNT baseline fluorescence. Based on our molecular dynamics andexperimental results, we hypothesized that tuning the surface density of(GT)₆ on the SWNT surface will affect the resulting SWNT electrostaticfootprint, and thus enable more precise control of the baselinefluorescence of the DNA-SWNT conjugate. We therefore varied polymersurface packing by synthesizing DNA-SWNT conjugates with different massproportions of SWNT (mS) and ss(GT)₆-DNA (mD). The resulting DNA-SWNTconjugates thus had variable surface-adsorbed polymer density. Weprepared three suspensions at mS/mD mass ratios of 2, 5 and 10. Theresulting fluorescence intensity from equimolar SWNT aliquots shows aclear trend whereby higher polymer surface densities (mS/mD=2) exhibitthe strongest fluorescence quenching. Addition of 10 μM of dopamineenhances the SWNT fluorescence of all three samples; however, thenanosensor response is highest for the SWNT sample (mS/mD=2) that ismost strongly pre-quenched prior to dopamine addition. These resultsreveal that (i) the degree of fluorescence quenching of SWNT by adsorbedDNA is a function not only of polymer conformation (ring vs. helix) butalso of the polymer surface density; the greater the surface coverage,the stronger the SWNT PL quenching; (ii) the higher the surfacecoverage, the higher the number of dopamine binding pockets; and (iii)dopamine enhances quantum yield in proportion to the number of availablebinding sites.

REFERENCES

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2. Yang, M., V. Koutsos, and M. Zaiser, Interactions between polymersand carbon nanotubes: a molecular dynamics study. The Journal ofPhysical Chemistry B, 2005. 109(20): p. 10009-10014.

3. Johnson, R. R., A. T. C. Johnson, and M. L. Klein, Probing thestructure of DNA-carbon nanotube hybrids with molecular dynamics NanoLetters, 2008. 8(1): p. 69-75.

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6. Landry, M. P., et al., Comparative dynamics and sequence dependenceof DNA and RNA binding to single walled carbon nanotubes. The Journal ofPhysical Chemistry C, 2015. 119(18): p. 10048-10058.

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8. Schöppler, F., et al., Molar extinction coefficient of single-wallcarbon nanotubes. The Journal of Physical Chemistry C, 2011. 115(30): p.14682-14686.

9. Choi, J. H. and M. S. Strano, Solvatochromism in single-walled carbonnanotubes. Applied Physics Letters, 2007. 90(22): p. 223114.

10. Tu, X., et al., DNA sequence motifs for structure-specificrecognition and separation of carbon nanotubes. Nature, 2009. 460(7252):p. 250-253.

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12. Salem, D. P., et al., Chirality dependent corona phase molecularrecognition of DNA-wrapped carbon nanotubes. Carbon, 2016. 97: p.147-153.

3. An Optical Nanosensor for Imaging Dopamine Neuromodulation in theExtracellular Space of Striatal Tissue

In this example we designed a nanoscale near-infrared fluorescentreporter for neuromodulator dopamine and demonstrate its efficacy forimaging dopamine volume transmission in the extracellular space of boththe brain striatum and cortex. The nanosensor images dopamine releaseand reuptake dynamics in the extracellular space arising from evoked aswell as spontaneous release with few-terminal spatial resolution. Weshow that dopamine volume transmission exhibits highly heterogeneousbehavior with apparent dopamine reuptake constants that span over anorder of magnitude. Inhibiting dopamine reuptake with antidepressantdrug nomifensine reveals that dopamine clearance is predominantlydiffusion mediated immediately following release, but dopaminetransporter mediated at longer times after release. We observespatially-correlated dopaminergic signaling dynamics, indicating brainregions of high release synchrony in the striatum. The probe reportsdopamine volume transmission at spatial scales that have heretofore beeninaccessible with existing investigative tools and can be employed torelate extracellular dopamine concentration dynamics with extrasynapticreceptor activation, neuronal activity, and behavior.

Herein we report a near-infrared fluorescent nanosensor for dopamine(nIRDA) that effectively records dopamine neuromodulation in mouse brainslice preparations. The sensor is synthesized by non-covalentlyconjugating a (GT)₆ polynucleotide sequence to fluorescent single wallcarbon nanotubes (SWNT). The sensor provides a reversible up to 3000%ΔF/F fluorescent response upon exposure to dopamine, which is used toimage transients in ECS dopamine concentration. The nanosensor provideshomogenous labeling of brain tissue, which affords terminal-levelspatial resolution, and sensor-analyte binding kinetics that enablevideo-rate recording of fluorescence modulation with high ##-ms temporalresolution. Our results demonstrate neurochemical imaging of dopaminedynamics in the striatum and cortex ECS with relevance for in vivoinvestigation of dopamine's critical functions in goal-directed behaviorand motor control, and dysfunctions that lead to disease.

Dopamine transients in acute brain slices can be imaged usingnear-infrared nanosensors

We designed near-infrared fluorescent dopamine sensors (nIRDAs) thatreport on dopamine in the extracellular space of neuronal tissue. nIRDAsare synthesized from single wall carbon nanotube (SWNT) fluorescentreporters electrostatically conjugated with synthetic polymers to buildnanometer-scale probes that can selectively report on local dopamineconcentration through a near-infrared change in fluorescence (ΔF/F) ofup to 3000% and with a dynamic range of uM to nM dopamine nIRDAs exhibitstrongly quenched baseline fluorescence and yield a strong turn-onfluorescent response selectively in the presence of dopamine.Fluorescent nanosensor parameters previously determined as optimalenable nIRDAs to capture low amplitude transients in dopamineconcentration arising from the activity of just a few boutons.

We chose to validate nIRDAs by imaging dopamine neuromodulation in acutestriatal brain slices. The striatum is a large subcortical structurewith homogenous and dense enervation by dopaminergic projections fromthe SNc. The striatum also receives major glutamatergic afferents fromthe cortex, whereas medium spiny neurons (MSN), the resident neurons ofthe striatum are GABAergic. Furthermore, cholinergic interneuronsfeature prominently in the striatum. nIRDAs exhibit strong selectivityfor dopamine over competing neurotransmitter molecules GABA, glutamate,and acetylcholine. We prepared coronal mouse brain slices, which weincubated with 5 mg.L⁻¹ of nIRDAs for 10 minutes to enable sensors tolocalize into the brain tissue. Slices were subsequently rinsed toremove excess or unbound nIRDAs. We found that this method affordedextensive and homogenous labeling of most parts of the coronal slice,including the dorsal striatum, where imaging of dopamine neuromodulationis performed. Furthermore, prior work confirms that SWNT-basedfluorophores localize in the ECS of brain tissue.

To image neuromodulation in the striatum with nIRDAs, we evoked dopaminerelease using both high potassium stimulation (K-stim) and withselective optogenetic stimulation of dopaminergic terminals (L-stim),which ensures that only dopamine is released into synaptic clefts andthe ECS. For L-stim, brain slices were prepared from mouse that werevirally transfected to express the light sensitive ion channel,channelrhodopsin (Chr2), in dopaminergic terminals of the striatum. Uponoptical stimulation with a 473 nm laser, we observe fluorescencemodulation of nIRDAs embedded in striatal tissue. The fluorescencemodulation is transient whereby its onset coincides with time ofstimulation, and is spatially colocalized with dopaminergic boutonsexhibiting high degree of Chr2 expression. When slices are labeled withSWNT-polymer constructs that are insensitive to dopamine, no modulationin fluorescence is observed upon repeated stimulation by light.Furthermore, slices that do not express Chr2 in dopaminergic terminalsare insensitive to light stimulation as shown by a lack of fluorescencemodulation of nIRDAs. Stimulation of wild type striatal tissue sliceswith high potassium ACSF buffer (15 mM-20 mM K⁺ ions) also elicits nIRDAfluorescence transients. While light-stimulated dopamine release eventsin optically active slices are instantaneous and exhibit fast releaseand re-uptake dynamics (˜2 s), stimulation by K⁺ produces dopaminedynamics that are considerably slower (˜10 s). During the course ofimaging experiments, we also observe nIRDA fluorescence transients thatare not elicited by stimulation but rather occur spontaneously, which weattribute to tonic dopamine release and re-uptake. These resultscollectively indicate that nIRDAs represent an imaging platform to probedopamine kinetics in the brain ECS.

Spatial analysis of nIR-DAS fluorescence modulation. A key benefit ofimaging neuromodulation lies in the temporally-resolved spatialinformation that can be garnered from imaging evoked and spontaneousdopamine release. Dopamine concentration transients in the ECS have beenstudied using electrochemical techniques such as FSCV. Despite thenotable role FSCV has played in elucidating DA dynamics in the ECS, itis a tool that assays overflow from the ensemble activity of hundreds ofdopaminergic terminals; it is not suited for capturing terminal levelspatial information because of the size of the carbon fiber electrode.As a result, information about dopamine volume transmission atinterterminal distances has remained largely inaccessible, and theinformation collected reports on the average behavior of hundreds ofterminals, averaging heterogeneities that may be present in individualsynapses. nIRDAs provide the spatial granularity required to probeterminal-scale dopaminergic activity to visualize local heterogeneitiesin dopamine reuptake, the temporal synchrony of release from terminalclusters, and the diffusive evolution of release from a single terminal.

In a representative recording, we analyzed the activity of seven highlyactive regions of interest (ROI) exhibiting spontaneous (non-evoked)dopamine release and reuptake activity. The regions examined spread over˜100 μm and exhibited synchronized dopamine activity. Correlationanalysis revealed the presence of two ROI clusters with highintracluster synchrony and high intercluster asynchrony despite theirspread over a 100 μm distance. Our results indicate that neurons cansynchronize dopamine release over hundred-micron distances, which issurprising considering that neurotransmitter release is a highlystochastic process with low release probabilities (<10%) fordopaminergic terminals in the striatum. Equally remarkable is the strongasynchrony observed between the two clusters, which indicates theclusters belong to two distinct projection axons with overlappingstriatal arborizations. This type of synchronized behavior is observedduring imaging of evoked dopamine release as well.

During evoked activity imaging, nIRDA fluorescence modulations can bespatially confined, or can evolve across the imaging field of view,enabling temporal analysis of the spatial evolution of dopamine in theECS. We present an example of light-stimulated dopamine release forwhich the spatial granularity afforded by nIRDAs enables tracking ofdopamine fluorescence hotspots over a spatio-temporally correlatedtrajectory. Upon evoked release of dopamine from a terminal or clusterof terminals, a sharp and localized increase in fluorescence and quickclearance thereafter results in the formation of fluorescence hotspotsthat travel as a function of distance from the release hotspot. Thissignal attenuates by diffusion and DAT mediated clearance. Analysis ofhot spots over their spatial and temporal trajectories reveals theevolution expected from diffusion of molecules from a point of highconcentration and their subsequent reuptake as a function of distance.We calculate a propagation of dopamine signal in the ECS exhibiting aquick attenuation in amplitude of ˜60% within a 20 μm distance with atemporal delay in the signal of 2 s at a distance of 70 μm from the hotspot.

Kinetic analysis of nIRDAS fluorescence transients. We analyzed kineticsof dopamine modulation from nIRDA fluorescence for evoked (L-stim,K-stim) and non-evoked activity recordings. For each preparation, weanalyzed dopamine reuptake rates over multiple slices in the ECS. Thedopamine reuptake kinetic parameter, which we report as the ratio of thereuptake rate r_(max) to the Michaelis constant K_(m)(k_(uptake)=r_(max)/K_(m)), enabled us to compare dopamine reuptakekinetics based on stimulation method. L-stim and non-evoked dynamicsyield fastest dopamine reuptake behavior. In comparison, K-stim slicesshowed an order of magnitude slower dopamine reuptake, likely aconsequence of high concentration of K⁺ ion on the performance of DATs.

We started with an in-vitro sensor calibration curve modified to accountfor nanosensor saturation by basal dopamine concentrations ex vivo andin vivo. Michaelis-Menten kinetic behavior for dopamine reuptake enablesus to extract the parameter r_(max) for select ROIs from the imagingfield of view.

Dopamine reuptake inhibitor nomifensine is a common antidepressant drugmarketed under Merital or Alival, and slows the clearance of dopaminefrom the ECS. Nomifensine competitively binds to dopamine transporters,membrane proteins that mediate the reuptake of dopamine, effectivelylowering the affinity parameter between dopamine and dopaminetransporters. To further investigate dopamine reuptake kinetics, weperformed K-stim and L-stim slice experiments in aCSF solutioncontaining 10 μM nomifensine. Following stimulation, we observe anextended persistence in the fluorescence of nIRDAs, consistent with theanticipated slowdown in dopamine clearance from the ECS. Quantitativeanalysis of dopamine reuptake kinetics shows that application ofnomifensine produced significant slowdown in clearance rates for bothL-stim and K-stim slices. While the effect of the nomifensine ondopamine clearance is expected, a closer examination of the clearanceprofile reveals a surprising presence of two distinct regimes. In thefirst regime, nIRDA fluorescence falls quickly following dopaminerelease, as expected for DAT-mediated dopamine clearance. The seconddopamine clearance regime follows, in which a sudden transition toslower dopamine reuptake is observed. This phenomenon is consistentlyobserved in all striatal brain slices bathed in nomifensine (10 μM). Ourresults indicate the existence of two dopamine clearance regimes fromthe ECS. In the first regime, the diffusive flux out of volume is thepredominant means by which dopamine concentration decreases. Dominantdiffusive clearance occurs immediately following stimulation and releaseof dopamine The dynamics of this regime is governed predominantly by theeffective diffusivity of dopamine in the ECS and the relative proximityof the volume of interest to the release site, and is unaffected by thepresence of reuptake inhibiting drugs. In the second regime,DAT-mediated clearance is predominant, in which dopamine reuptakedynamics can be manipulated by drugs that interfere with the DAT-DAaffinity parameter.

Analyzing the rise rate of nIRDA fluorescence signals further bolstersour hypothesis of the presence of two dopamine clearance regimes. Thedopamine concentration rise rate is a function of proximity to thereleasing dopaminergic terminal. Signals obtained from ROIs that areproximal to the dopamine-releasing terminal will show higher rise ratescompared to ROIs that are located distal to release sites. Rise ratestherefore provide a measure of an ROI's proximity to the releasingterminal. If diffusion mediated clearance is an important component ofthe computed apparent reuptake constant, k_(uptake), its magnitude willshow a positive correlation with proximity to dopamine release sites,and importantly, to the rise rate. This positive correlation is indeedapparent for all evoked and non-evoked data we analyzed. To furthersubstantiate our findings, we implemented a stochastic simulation ofdopamine neuromodulation in the dorsal striatum in the presence andabsence of nomifensine. Our simulation probes the spatial evolution of asingle quantal release of dopamine in the presence (K_(m)=8 μM), andabsence (K_(m)=0.2 μM) of nomifensine, and reveals that the clearance ofdopamine exhibits dual behavior at distances close to the releasingterminal. The model predicts that close to the releasing terminal thediffusive clearance of dopamine is the dominant process, and thusnomifensine minimally affects the reuptake of dopamine Conversely, inthe absence of nomifensine, our model recovers the quick DAT-mediateddopamine reuptake behavior we observe in nomifensine-free sliceexperiments. Our results illuminate two dopamine reuptake clearanceregimes in the presence of a DAT-mediated reuptake inhibitor, regimeslikely not observed in data from FSCV measurements in which the spatialprofile of dopamine release is averaged over hundreds of termini.

1. A functionalized, neurocompatible single-walled carbon nanotube(SWNT) comprising an adsorbed neurotransmitter analyte selectivepolynucleotide covalently bound to a neurocompatible polyethyleneglycol(PEG).
 2. The nanotube of claim 1 wherein the polynucleotide is ssDNA orssRNA
 3. The nanotube of claim 1 wherein the polynucleotide has aperiodic purine-pyrimidine pattern.
 4. The nanotube of claim 1 whereinthe polynucleotide is ssDNA or ssRNA; and the polynucleotide has aperiodic purine-pyrimidine pattern.
 5. The nanotube of claim 1 whereinthe polynucleotide is ssDNA or ssRNA; and the polynucleotide is polyGTis (GT)n, wherein n is an integer 4-30.
 6. The nanotube of claim 1wherein the polynucleotide is ssDNA or ssRNA; and the polynucleotide ispolyGT is (GT)n, wherein n is
 6. 7. The nanotube of claim 1 wherein theanalyte is a neurotransmitter selected from a catecholamine (e.g.epinephrine (adrenaline), norepinephrine (noradrenaline), and dopamine),histamine, 5-hydroxytryptamine (serotonin), γ-aminobutyric acid (GABA),glutamine, glutamic acid or a neurotransmitter metabolite selected fromL-3,4-dihydroxyphenylalanine (L-dopa), 3,4-Dihydroxyphenylacetic acid(DOPAC), homovannilic acid and tyramine
 8. The nanotube of claim 1wherein the analyte is dopamine.
 9. The nanotube of claim 1 wherein thePEG is PEG MW 400-20000.
 10. The nanotube of claim 1 wherein the analyteis dopamine; and the PEG is PEG MW 400-20000.
 11. The nanotube of claim2 wherein the analyte is dopamine; and the PEG is PEG MW 400-20000. 12.The nanotube of claim 3 wherein the analyte is dopamine; and the PEG isPEG MW 400-20000.
 13. The nanotube of claim 4 wherein the analyte isdopamine; and the PEG is PEG MW 400-20000.
 14. The nanotube of claim 5wherein the analyte is dopamine; and the PEG is PEG MW 400-20000. 15.The nanotube of claim 6 wherein the analyte is dopamine; and the PEG isPEG MW 400-20000.
 16. A functionalized, neurocompatible single-walledcarbon nanotube (SWNT) comprising an adsorbed dopamine-selectivepolynucleotide of sequence (GT)₆.
 17. The nanotube of claim 16 whereinthe polynucleotide is covalently bound to a neurocompatiblepolyethyleneglycol (PEG).
 18. The nanotube of claiml6 wherein the PEG isPEG MW 400-20000.
 19. The nanotube of claim 16 wherein thepolynucleotide is covalently bound to a neurocompatiblepolyethyleneglycol (PEG); and the PEG is PEG MW 400-20000.
 20. A methodof imaging comprising: detecting changes in extracellularneurotransmitter concentration with the nanotube of claim 1 wherein thechanges in extracellular neurotransmitter concentration are detected inneural tissue, and the nanotube is delivered to and/or located in livebrain tissue in a brain slice or live mammal.